Self-illuminated handheld lens for retinal examination and photography and related method thereof

ABSTRACT

System and method directed towards providing full and even illumination of a patient&#39;s retina through lighting integrated into a handheld fundus lens. By integrating the lighting, the method and system reduces and even eliminate many lens artifacts and reflections. By increasing the accuracy, quality, and field of view 10 afforded during clinical examination of the retina, the method and system will allow practitioners to make more accurate diagnoses and will increase safety during retinal surgical procedures.

RELATED APPLICATIONS

This application is a continuation application under 35 U.S.C. § 120 ofU.S. patent application Ser. No. 15/048,279, filed Feb. 19, 2016, whichis a continuation-in-part (CIP) application of U.S. patent applicationSer. No. 14/268,643, filed May 2, 2014, now U.S. Pat. No. 9,265,410,granted on Feb. 23, 2016, which is a division of U.S. patent applicationSer. No. 13/318,695, filed Nov. 3, 2011, now U.S. Pat. No. 8,740,383,granted on Jun. 3, 2014, which is a national stage filing ofInternational Application No. PCT/US2010/033875, filed May 6, 2010,which claims the benefit of priority under 35 U.S.C. § 119(e) of U.S.Provisional Application Ser. No. 61/175,807, filed on May 6, 2009,entitled “Self-Illuminated Handheld Lens for Retinal Examination andPhotography and Related Method thereof;” the disclosures of which arehereby incorporated by reference herein in their entirety.

FIELD OF THE INVENTION

The present invention is directed to an improved device for retinalexamination and related methods. More specifically, aspects of thepresent invention are directed to handheld fundus lenses with integratedlighting that are self-contained.

BACKGROUND OF THE INVENTION

Clinical examination and treatment of retinal disease has notfundamentally changed in the last 100 years, relying on a slit lampbiomicroscope which consists of a binocular stereo microscope, ahandheld condensing lens, and a slit lamp providing illumination toexamine the retina, as seen in FIG. 1A. A slit beam of light is createdby the slit lamp and shone through a handheld lens placed in front ofthe patient's eye. The handheld lens produces an image that isvisualized through the oculars of the biomicroscope. Unfortunately, thistechnique suffers from significant image aberrations induced by lightreflections off the handheld lens, which limits the practical view toonly a thin slice of retina comprising less than 1% of the total retinasurface area. FIG. 1B is a typical image of the retina provided by slitbeam illumination and a handheld lens. Note the limited field of viewand significant lens reflections present. The position of the slit mustbe maneuvered to examine different parts of the retina. Image qualityeven from this slit is often significantly degraded, making retinaldiagnosis difficult. In contrast, conventional retinal photographyroutinely is capable of 50 degree aberration and reflection free fieldsof view of the retina. FIG. 1C is a standard fundus camera image of aretina. There is significantly greater retinal detail and a much widerfield of view compared to the slit lamp image of FIG. 1B. No lensreflections or image aberrations are present, greatly facilitatingdiagnosis of retinal diseases. Unfortunately, these photographicadvances have yet to be translated in any meaningful way intoimprovements in the clinical exam.

There are currently 16 million diabetic patients in the United Stateswho require yearly, dilated retina exams as part of their recommendedeye care. Half of these patients will have some form of retinopathypresent at the time of exam. For the majority of these patients, slitlamp retinal examination is the only modality used to document theirretinal findings. Retina photos are used as an adjunct to the clinicalexam in only 10-20% of patients, as this involves separate timeconsuming procedures by the ophthalmic photographer. This makes itimperative that a clear and reliable view of the retina is available tothe clinician for accurate diagnosis.

Ten percent of diabetic patients will eventually develop proliferativediabetic retinopathy, requiring panretinal laser photocoagulation (PRP)to ablate their peripheral retina in an attempt to preserve centralfoveal vision. FIG. 2A illustrates a retina after PRP. Laserphotocoagulation may be delivered via slit lamp techniques usingwidefield (>75 degree field of view) handheld lenses. These lenses,relying on the same slit illumination, suffer significantly greaterreflection artifacts than the narrow field (<75 degree field of view)handheld lenses used for clinical exam of the macula. FIG. 2Billustrates a clinician's view at a slit lamp while performing PRP. Ahandheld contact lens is applied to a patient's eye and slit lampillumination is used to visualize the retina and the aiming beam for thelaser. Retinal detail is severely compromised from lens reflections andthe limited field of view afforded by the slit illumination. The risk ofinadvertent laser to the fovea is significant due to the obscuration ofthe optic nerve by this pattern of poor illumination and lensreflections. The slit beam must be constantly moved to reorient to thelocation of the optic nerve to verify retinal position and avoidinadvertent ablation of the central vision with laser. The limited andgenerally poor illumination provided by the slit beam substantiallyincreases the time required for laser treatment and poses a significantand unnecessary safety hazard due to poor identification of retinallocation.

Many diabetic patients with proliferative diabetic retinopathy proceedto develop chronic vitreous hemorrhages and decreased vision, requiringsurgical removal of the blood in some cases. Poor illumination alsoposes a safety hazard for their retinal surgery. Standard pars planavitrectomy technique relies on fiber optic illumination provided by arigid 20 or 23 gauge probe inserted through the pars plana of the eye.Limited beam divergence of the fiber optic probe provides spotillumination of the retina, with details of the surrounding peripheralretina remaining poorly illuminated, as seen in FIG. 2C. This leads toan increased likelihood of instrument error causing permanent retinaldamage. Greater surgical safety and decreased surgical times would befacilitated by a widefield general illumination of the retina inaddition to the spot illumination provided by the fiber optic probe.

Commercial developments in ophthalmic photography over the last 40 yearshave clearly demonstrated that the retina can be imaged at highresolution and that image distortions/reflections can be fully correctedto enable accurate diagnosis of retinal disease. The hallmark of thedifference in retinal photography over clinical exams is the differentpattern of illumination used in each, as illustrated in FIG. 3A.Contemporary retina cameras generate a ring or “donut” of illuminationcentered on the pupil. This circular illumination provides an even/fullillumination of the retina with minimal lens reflections. Imaging raysreflected from the back of the retina are collected from the middle ofthe “donut,” which substantially decreases lens reflections. Mostcommercial retina cameras are able to obtain a 50 degree field of viewof the retina with this technique FIG. 1C, but are not able to achievewidefield (>75 degrees field of view) images such as shown in FIG. 2A.

Narrowfield cameras are non-contact, with the camera never touching thefront surface of the eye. In contrast, widefield cameras often requiredirect contact of the imaging system with the cornea. The commercialRETCAM II retinal camera is an example of a widefield camera whichdirectly contacts the cornea. This camera creates a donut of light usinga solid fiber optic ring to couple an external illumination lightdirectly to the cornea, as shown in FIG. 3E. FIG. 3C shows a sampleimage from the Retcam II. This illumination design, while a significantimprovement on slit lamp illumination, still suffers from significantcorneal haze, as well as unevenness in central illumination, as comparedto peripheral illumination, due to issues with the illumination design.Further, the RETCAM II is designed for retinal photography and asspecified is not capable of use in handheld clinical examination througha slit lamp biomicroscope. The device has electrical power and fiberoptic light coupled into a sizable imaging wand that is significantlylarger than existing handheld fundus lenses, severely limiting theunit's portability and ease of use. The design of the illuminating ringrequires intricate manufacturing that would not be amenable toinexpensive handheld lenses. All these issues are addressed in variousembodiments of the present invention, which is a significant improvementover contemporary designs.

An improved method of illumination is needed to provide a wider field ofview of the retina and to eliminate those lens reflections that resultfrom external slit illumination of the handheld condensing lens. Theideal illumination for the retina is a ring of light focused on the eyewith a diameter slightly less than the pupil diameter. Prior designs(Pomerantzeff et al., U.S. Pat. No. 3,944,341, and Massie et al., U.S.Pat. No. 5,822,036, of which are incorporated by reference herein intheir entirety) have adapted a method of illumination into designs forretinal photography, as opposed to clinical examination. These twodesigns rely on an external illumination device that is then routed bymeans of fiber optic coupling into a contact lens that is used to viewthe retina.

These existing devices, while may be an improvement over non-illuminatedhandheld lenses, suffer from a number of design constraints that do notallow them to be used for handheld fundus examination at the ophthalmicslit lamp. Pomerantzeff relies on two rows of individual fiber opticelements that are cemented into a contact lens with the fiber opticsdirectly contacting the cornea. This presents issues with sterilizationdue to the inevitable breakdown of the cementing compound and lodging ofbacteria into the cemented area surrounding it. It also requirestechnically difficult fiber optic polishing so that the individualfibers do not damage the cornea and are all at the same plane. Byfocusing the ring of light on the cornea through means of fiber optics,significant corneal haze is generated which lowers overall imagecontrast. There is a complicated five stage optical element design toproduce an image which leads to an unnecessarily bulky lens that couldnot be easily manufactured or handheld due to its overall size. Thedirectionality of the fiber optics, while illuminating some of theperipheral retina, do not illuminate the central portion of the retinawell, leaving the macula less exposed to light compared to theperipheral retina. A separate illuminator is required that is externalto the device, requires electrical power, and limits portability of thisdevice. The device is intended for retinal photography and is notoptimized or usable for slit lamp examination. The focus of the fivelens design is intended to focus reflected retina light on an imagingdevice directly attached to the lens, rather than at the distancesrequired by ophthalmic slit lamp examination. Finally, the patent hasnot resulted in a commercial device in the 30 years since it wasoriginally issued.

The patent by Massie et al. has similar limitations to the earlierdesign of Pomerantzeff. Fiber optic illumination is used to direct thelight from an external illumination source into the imaging lens,reducing portability of the unit. The device is intended only forretinal photography with an imaging device built into the handheld unitand then electrically connected to a larger external imaging controlunit. There is no clear optical axis that would allow use of the deviceat the ophthalmic slit lamp. The design is intended to focus the lightfrom the retina onto an imaging device that is located directly behindthe contact lens rather than at the distances required by handheldcondensing lenses used at an ophthalmic slit lamp. The use of fiberoptics for coupling of an external illumination source limits thediffusion of the illuminating light beam and provides only partialillumination of the retina with a dark central retina, as also seen withthe Pomerantzeff design. While the Massie design allows for illuminationby placing a second central illumination source contained within thehandheld unit itself to illuminate central retina, it obscures thecentral axis of the lens, which eliminates visualization of the retinathrough the center of the lens; a function essential to a handheldcondensing lens. The design additionally attempts to improve theillumination produced by fiber optic through use of up to threeadditional lens elements at the end of the fiber optic, which againcomplicates construction and alignment of this device. Similar to thePomerantzeff design, Massie's coupling of light fiber optically directlyto the corneal surface results in significant corneal haze whichdegrades image contrast.

Fine polishing of the fiber optic is required to angle the exit of thelight to improve the area of the retina illuminated. However, the anglecut required on the fiber optic reduces transmission of the light due tothe oblique exit of the light from the fiber optic element. Finally, thedesign of the Massie device results in a bulky imaging unit that farexceeds the typical 40 mm depth of a handheld fundus lens. All of thesedesign issues that are optimized for retinal photography limit theability of this design to be used as a self illuminated handheldcondensing lens for retinal examination.

Next, Miller et al., U.S. Pat. No. 7,048,379, discloses an imaging lensand illumination system for a retinal camera. Miller's ring illuminationwas focused on the patient's retina through a front objective lens. Thelighting is located behind the objective lens, and the camera is notdesigned with a contact lens.

Contemporary retinal photography designs are capable of attaining betterquality images and a wider field of view with less reflections thanconventional slit lamp illumination. However, they remain limited bysize, portability, poor illumination, and poor image contrast. Massieand Pomerantzeff produced devices which have no direct view through thelens that is available for the practitioner to directly visualize theretina (as both are intended for retinal photography) and are too largeto be of practical use in clinical examination. Further, theircomplicated designs render them expensive to manufacture. Finally, theystill suffer from problems with full and even illumination.

Providing the versatility and speed of clinical examination with theaccuracy and clarity of retinal photography would provide greatlyimproved image quality, permitting significantly wider fields of view,better resolution of retinal detail for diagnosis, and safer surgicalintervention to treat retinal disease.

SUMMARY OF THE INVENTION

An aspect of an embodiment of the present invention seeks to correct theillumination issues with current handheld fundus lenses. The slit lampbiomicroscope may be used to view the image through the handheld retinalens, but the handheld lens itself would provide the illumination of theretina, rather than relying on slit illumination provided by the slitlamp. An aspect of various embodiments of the present invention capturesthe illumination characteristics of retinal camera design in miniature,creating a design that may be battery powered and simple to manufacture,maintaining commercial viability. An embodiment provides, among otherthings, a handheld lens where ring illumination is directly coupled tothe contact lens portion of the handheld lens, as illustrated in FIG.3B. This creates a ring or “donut” of illumination that is transmittedto the eye when the front contact lens of the device is applied to thecornea. This ring could be created through many designs, including aring of surface mount LEDs, the use of fiber optics to fashion donutillumination from a point source of light, the use of a shaped mirror toprovide a dispersed donut of light, and a curved surface with surfacemount LEDs providing multidirectional illumination. FIG. 3D illustratesthe potential viewing area of such a widefield handheld contact imaginglens of FIG. 3B.

An aspect of an embodiment of the present invention provides aself-illuminated handheld lens (and related method) to aid in theexamination and treatment of retinal disease. Retinal exams and retinallaser treatments are commonly performed using a slit lamp biomicroscope.The slit lamp uses a narrow beam of light that illuminates less than 1%of the total retinal surface and suffers from significant opticalaberrations that obscure retinal details. To alleviate these problems,an embodiment of the present invention provides a self-illuminatedhandheld fundus lens for retinal imaging to be used in conjunction withthe slit lamp biomicroscope to provide clear, reflection free, widefield illumination and view of the retina. An aspect of an embodiment ofthe present invention device creates ring illumination that is coupledthrough the contact lens of a handheld fundus lens to provide thiswidefield illumination of the retina. An embodiment of the presentinvention device may rely on use of fiber optics and/or light emittingdiodes to provide illumination, though many other means of illuminationare possible.

An aspect of an embodiment of the present invention provides aself-illuminated handheld device for retinal examination of a subject.The device may comprise: a viewing lens; a contact lens to be applied toan eye; an integrated light source; an annular light channel throughwhich light from the integrated light source is transmitted to the eye;and a light baffle separating the integrated light source and the lightchannel from a central aperture between the viewing lens and the contactlens.

An aspect of an embodiment of the present invention provides a systemand related method for retinal photography. The system includes aself-illuminated handheld fundus lens, whereby the self-illuminatedfundus lens may comprise: a viewing lens; a contact lens to be appliedto an eye of a subject; an integrated light source; an annular lightchannel through which light from the integrated light source istransmitted to the eye; and a light baffle separating the integratedlight source and the light channel from a central aperture between theviewing lens and the contact lens. Moreover, the system may alsoinclude: an image recording device; and a lens-to-camera interface,adapted to transmit an image from the lens to the image recordingdevice.

An aspect of an embodiment of the present invention provides aself-illuminated handheld device (and related method) for retinalexamination of a subject. The device may comprise: a viewing lens; acontact lens to be applied to an eye; an integrated light source; anannular light channel through which light from the integrated lightsource is transmitted to the eye, the annular light channel is athinning of the contact lens, a portion of the contact lens that differsin power, a gap ground into or provided in the contact lens, a gaparound or adjacent to the contact lens, or a space behind or adjacent tothe contact lens and is located behind, around, adjacent to or throughthe contact lens; a light baffle separating the integrated light sourceand the light channel from a central aperture between the viewing lensand the contact lens; and an integrated power source in communicationwith the integrated light source.

An aspect of an embodiment provides a self-illuminated handheld lens forwide angle retinal viewing of a subject eye, comprising: an asphericalobjective lens having a symmetric viewing axis and defining a viewingchannel; plurality of LEDs positioned around the viewing axis andconfigured to emit light to illuminate the subject eye; an electroniccontroller powering the plurality of LEDs and controlling eachindividual LED or a series of LEDs independently; a light baffleconfigured to block stray light of the plurality of LEDs from gettinginto the viewing channel; and a cross polarization means incorporatedbetween the plurality of LEDs and the viewing channel of the asphericalobjective lens, wherein the cross polarization means comprises a firstpolarizer to polarize the light emitted from the plurality of LEDs and asecond polarizer positioned in the viewing channel of the asphericalobjective lens. An aspect of an embodiment of the present inventionprovides a method (and related system) for illuminating thecornea/retina of an eye of a subject through a handheld device. Themethod may comprise: generating light from one or more light sources;reflecting the light off a mirrored surface; transmitting the lightthrough an annular light channel proximal to a contact lens; andreceiving an illuminated image from the eye through a viewing lens.

These and other objects, along with advantages and features of variousaspects of embodiments of the invention disclosed herein, will be mademore apparent from the description, drawings and claims that follow.

BRIEF DESCRIPTION OF THE DRAWINGS

The accompanying drawings, which are incorporated into and form a partof the instant specification, illustrate several aspects and embodimentsof the present invention and, together with the description herein,serve to explain the principles of the invention. The drawings areprovided only for the purpose of illustrating select embodiments of theinvention and are not to be construed as limiting the invention.

FIG. 1A illustrates a slit lamp biomicroscope.

FIG. 1B demonstrates a typical image provided by a slit lampbiomicroscope with use of a contemporary handheld lens and standard slitlamp illumination.

FIG. 1C demonstrates a typical image provided by a fundus camera, withthe same scale as used in FIG. 1B.

FIG. 2A illustrates a retina after undergoing panretinalphotocoagulation (PRP) for treatment of proliferative diabeticretinopathy.

FIG. 2B illustrates a clinician's view at a slit lamp biomicroscopeduring performance of PRP using a contemporary widefield handheld lenswith standard slit lamp illumination.

FIG. 2C illustrates a retina surgeons's view through an operatingmicroscope during pars plana vitrectomy surgery.

FIG. 3A illustrates the typical “donut” illumination used by mostcommercial retina cameras.

FIG. 3B illustrates an embodiment of the present invention handheldfundus lens that provides its own ring illumination built into itscontact lens.

FIG. 3C demonstrates a sample image and design of a commercial retinacamera.

FIG. 3D illustrates the field of view obtained by the widefield lens ofFIG. 3B, which can visualize the full 165 degrees field of view of theretina.

FIG. 3E shows the commercial retinal camera, RETCAM II.

FIG. 4 schematically illustrates an embodiment of the present invention,utilizing fiber optic cables to couple light from either an externallight source, or a light source built into the handheld lens itself toilluminate the retina.

FIG. 5 schematically illustrates an embodiment of the present invention,utilizing light emitting diodes to illuminate the retina.

FIG. 6 schematically illustrates an embodiment of the present invention,utilizing a combination of fiber optic cables and a mirrored surface toilluminate the retina.

FIG. 7 schematically illustrates an embodiment of the present invention,utilizing a combination of light emitting diodes and a mirrored surfaceto illuminate the retina.

FIGS. 8A-B schematically illustrate a possible configuration ofcomponents in an assembled view and exploded view, respectively, thatcan be used to implement, for example, but not limited thereto, theembodiment shown in FIG. 7, which utilizes a combination of lightemitting diodes and a mirrored surface to illuminate the retina.

FIG. 9 schematically illustrates one embodiment of the presentinvention, utilizing a combination of xenon flash lighting and amirrored surface to illuminate the retina.

FIG. 10 schematically illustrates one embodiment of the presentinvention, utilizing light emitting diodes mounted on a curved surfaceto illuminate the retina.

FIGS. 11A-11B schematically illustrate the external casing of anembodiment of the present invention in side ways position and upwardposition, respectively.

FIGS. 12A-B illustrates a schematic view and a photographic depiction,respectively, of the use of an embodiment of the present invention aspart of a system for retinal photography.

FIG. 13A shows a view of a model eye using, for example, the embodimentof FIG. 10.

FIG. 13B shows a view of a model eye using, for example, the embodimentof FIG. 10.

FIG. 13C shows an image taken by a contemporary retinal camera. Theimage is obscured by corneal haze.

FIG. 14 shows schematically a wide field fundus camera implementedhaving a front LED illumination module.

FIG. 15 shows schematically an embodiment of the front LED illuminationmodule, and furthermore with cross polarization.

FIG. 16 shows schematically a self-illuminated wide angle contact lensimplemented a front LED illumination module with cross polarization.

FIG. 17 shows a CAD drawing of self-illuminated wide angle contact lensimplemented a front LED illumination module with cross polarization.

FIG. 18 shows a front view of FIG. 17 of a LED circular array for frontLED illumination.

FIG. 19 shows a side view of FIG. 17 of a LED circular array for frontLED illumination.

FIG. 20 shows a cross section drawing of a self-illuminated handheldlens implemented having a front LED illumination module with crosspolarization.

FIG. 21 shows a side view of the self-illuminated handheld lens of FIG.20.

FIG. 22 shows a front view of the self-illuminated handheld lens of FIG.20.

DETAILED DESCRIPTION OF THE INVENTION

Aspects of the present invention are directed towards providing full andeven illumination of a patient's retina through lighting integrated intoa handheld fundus lens. By integrating the lighting, aspects of thepresent invention reduce and even eliminate many lens artifacts andreflections. By increasing the accuracy, quality, and field of viewafforded during clinical examination of the retina, an aspect of thepresent invention will allow practitioners to make more accuratediagnoses and will increase safety during retinal surgical procedures.

An aspect of an embodiment of the current invention is designed toprovide, among other things, self-contained ring illumination of theretina within the space constraints of a handheld fundus lens whichmeasures approximately 40 mm×50 mm×20 mm, and optimized forvisualization of retinal details by a trained practitioner at anophthalmic slit lamp. As portability of the unit may be advantageous tomarketability and acceptance of this device, the design may be focusedon this design constraint for the various embodiments of this invention.While this specific size is the average size of a handheld lens, it willbe readily understood that larger lenses may still meet the handhelddesign constraint. We also consider other embodiments that meet some butnot all of these design constraints, as they may be preferred undercertain circumstances. It should be appreciated that the devices andsystems of the various embodiments discussed throughout this disclosuremay be implemented to be larger or smaller than the dimensions of 40mm×50 mm×20 mm, as desired or required.

Several embodiments of the present invention are discussed below.However, the invention may be embodied in other forms without departingfrom the spirit or essential characteristics of the present invention.It is therefore to be understood that the following embodiments are tobe considered illustrative rather than limiting of the inventiondescribed herein.

An embodiment of the present invention provides a handheld lens 11 forilluminating a patient's retina 101 from a point source of light throughfiber optics cables. This embodiment is illustrated in FIG. 4. In thisembodiment, there is a light source 1 outside of the lens that isdirectly coupled to fiber optic cable 2. Light source 1 may be anybright light. In one embodiment it would consist of a white, infrared,or color high intensity LED light source as these light sources have lowpower requirements amenable to battery power. In another embodiment itwould include halogen or xenon flash lighting which may or may notrequire electrical line power to achieve higher intensity illuminationthan could be provided by LEDs. The fiber optic cable 2 may be composedof multiple thin fiberoptic strands. These individual strands arereformed into a ring illumination that directly abuts the contact lens3. A light channel 4 is ground into the contact lens 3 and fiber opticcable 2 inserts into this light channel 4. The light channel 4 may bearound, through, adjacent or behind contact lens 3. It is through thelight channel 4 that light from the fiber optic cable 2 is transmittedto the retina 101. The light channel 4 may be a thinning of the contactlens 3, a portion of the contact lens 3 that differs in power, a gapground into or provided in the contact lens 3, a gap around or adjacentto the contact lens 3, or a space behind or adjacent to the contact lens3. The fiber optic cable 2 is located in a separate light cavity 5 ofthe handheld lens 11 with a light baffle 6 to prevent stray light fromentering the central aperture 12 of the lens cavity 15 and the viewingfield of a viewing lens 7. The sides of the light channel 4 are coveredwith material to prevent transmission of stray light from the lightchannel 4 into contact lens 3 which would obscure the image viewedthrough the viewing lens 7. Light from the light source 1, transmittedthrough the fiber optic cable 2 and light channel 4 to the retina 101,reflects back through the contact lens 3 and viewing lens 7 resulting inan image 100.

Contemporary designs utilized an angle cut and polished solid one-piecefiber optic insert to transmit light to the contact lens. As has beennoted, this has the disadvantage of decreasing transmission of lightfrom the end of the fiberoptic due to the oblique angle of the cut end.Further, light emerging from the end of the fiberoptic does not providea diffuse light source as is required to illuminate the entire retina.One aspect of the current invention solves this limitation through adiffusing insert. Two exemplary implementations are now described. Inthe first, the individual fiber optic strands of fiber optic cable 2enter a fiber optic block 8 perpendicular to its surface. The fiberoptic block 8 is optionally inserted into the light channel 4. Eachstrand of the fiber optic cable 2 is threaded into a hole in the fiberoptic block 8. The hole for each strand of the fiber optic cable 2 isprogressively angled so that the directionality of light from theindividual strands as they emerge at the distal end of the fiber opticblock 8 is different. This allows illumination to be directed fromindividual fibers both centrally and peripherally so that no differencein illumination occurs as was found in contemporary designs. A secondexemplary approach is to optionally embed a mini-optical diffuser 9within the light channel 4, replacing the fiber optic block 8. AMini-optical diffuser 9 scatters the incident light from the incomingstrands of the fiber optic cable 2, thereby reducing the strongdirectionality of the fiberoptic light. This provides more evenillumination with multidirectionality of light to provide evenillumination of both peripheral and central retina than contemporarydesigns. This is also a technically more efficient and pragmatic designthan the multiple added lens elements used in contemporary designs toreduce the directionality of the light.

In order to obtain selective illumination of the retina 101, anadjustable optical mask 16 may be used. This mask may be physical, suchas an adjustable diaphragm, or electronic, such as a transparent liquidcrystal display. Use of the adjustable optical mask 16 would allow aclinician to control which portion of the retina 101 is illuminated.

Another embodiment of the present invention provides a handheld lens 11utilizing a ring of light-emitting diodes (LEDs) to provide illuminationto the retina 101 and is illustrated in FIG. 5. The illustratedembodiment provides ring illumination directly within handheld lens 11using a ring of LEDs 10. LEDs 10 may be high intensity white, infrared,or colored. Utilizing different types of LEDs allows for imaging ofeither red free, infrared, or fluorescent dyes which are commonly usedto evaluate retinal function. In one implementation of this embodiment,an optical diffuser 13 is used to reduce the point sourcecharacteristics of the LEDs 10. The light from the LEDs 10 remainscontained within the light cavity 5 and light baffle 6 so that straylight does not enter the central aperture 12 of the lens cavity 15 orthe viewing area of the viewing lens 7. The light enters the lightchannel 4 and is transmitted to the retina 101. As the sides of lightchannel 4 are coated to block light from entering contact lens 3, aneffective optical circular ring mask is created. Light is onlytransmitted from the distal end of the light channel 4, directlyadjacent to the patient's cornea. It is through the light channel 4 thatlight from LEDs 10 is transmitted to the retina 101. The light channel 4may be a thinning of the contact lens 3, a portion of the contact lens 3that differs in power, a gap ground into or provided in the contact lens3, a gap around or adjacent to the contact lens 3, or a space behind oradjacent to the contact lens 3. Light from the LEDs 10, transmittedthrough the light channel 4 to the retina 101, reflects back through thecontact lens 3 and viewing lens 7 resulting in an image 100.

In cases where central or mid peripheral retinal illumination isrequired, this will provide sufficient even illumination of the retina.In instances where a wider field of illumination is needed, amini-optical diffuser 9 at the distal end of the light channel 4 is usedto scatter the illumination evenly across the entire retina. Analternative embodiment is to place a fiber optic ring block 8 into thelight channel 4. Small lengths of fiber optic strands 12 run throughoutthe fiber optic block 8. As in the preceding embodiment, the smalllengths of fiber optic strands 12 may be angled to redirect the light atall incident angles to provide full and even illumination of central andperipheral retina.

In some contemporary designs, two rings of fiberoptic illumination wereembedded into the contact lens to adjust for different pupil sizes.Either one or the other ring would be illuminated to provide the optimalretinal illumination. One aspect of the present invention proposes toaddress this by placing an adjustable optical mask 16 within lightchannel 4. The size of the adjustable optical mask 16, limiting theamount and shape of the light passing through the contact lens 3, may becontrolled by the practitioner according to required pupil size. Thismay be done either mechanically through manual adjustment of an embeddeddiaphragm or in an alternative embodiment an electronic transparent LCDis embedded into the light channel 4 and individual pixels arecontrolled electronically to set the size of the ring mask. Thus, thedevice can be used on multiple patients and the size of the ringillumination customized to their particular pupil size to provideoptimal retinal illumination.

In order to obtain selective illumination of the retina 101 by the LEDs10, a controller 17, such as a microcontroller, may be used. Thiscontroller 17 allows for control of which LEDs of LEDs 10 areilluminated, for how long (e.g., various temporal characteristics), andhow bright. Use of controller 17 would allow a clinician to controlwhich portion of the retina 101 is illuminated (e.g., pattern or spatialarrangement).

It should be appreciated that a controller and/or processor may be incommunication with any of the components or systems disclosed herein, asdesired or required.

Another embodiment of the present invention provides a handheld lens 11,which involves the use of an annular mirror to scatter light from alight source and transmit it to a patient's eye. One such embodiment isillustrated in FIG. 6. In this embodiment, the shape of the mirror isdesigned to create even illumination of both central and peripheralretina. The fiber optic cable 2 is used to transmit light from the lightsource 1 through the light cavity 5. The light source 1 may be anybright light. In an embodiment it may consist of a white, infrared, orcolor high intensity LED light source as these light sources have lowpower requirements amenable to battery power. In another embodiment itwould include halogen or xenon flash lighting, which may or may notrequire electrical line power to achieve higher intensity illuminationthan could be provided by LEDs. The fiber optic cable 2 may be composedof multiple thin fiberoptic strands. The light from the fiber opticcable 2 is then reflected off of the mirrored surface 21 through thelight channel 4 and contact lens 3, into the patient's eye. It isthrough the light channel 4 that light from the LEDs 10 is transmittedto the retina 101. The light channel 4 may be a thinning of the contactlens 3, a portion of contact lens 3 that differs in power, a gap groundinto or provided in the contact lens 3, a gap around or adjacent thecontact lens 3, or a space behind or adjacent to the contact lens 3. Inone embodiment, the mirrored surface 21 is designed to provide evenillumination of the retina by reducing the directionality of the light.The mirrored surface 21 also prevents light from entering the centralaperture 12 of the lens cavity 15 and the viewing area of the viewinglens 7. In this sense, the mirrored surface 21 serves a similar purposeto the light baffle 6. The focus point for the scattered light reflectedfrom the mirrored surface is not at the corneal surface as occurs withcontemporary fiber optic designs. This feature significantly reducescorneal haze that is present in contemporary designs. Light from thelight source 1, transmitted through the fiber optic cable 2, off of themirrored surface 21, and through the light channel 4 to the retina 101,reflects back through the contact lens 3 and the viewing lens 7resulting in an image 100.

A similar embodiment is illustrated in FIG. 7. This embodiment providesa handheld lens 11 which utilizes a ring of the surface mounted LEDs 10and a mirrored surface 21 to illuminate a patient's retina 101,providing a ring of light. Light from the LEDs 10 is emitted in thelight cavity 5. The LEDs 10 may be high-intensity white, infrared, orcolored. The light is reflected off of the mirrored surface 21 throughthe light channel 4 and contact lens 3, into the patient's eye. In anembodiment, the mirrored surface 21 is designed to provide evenillumination of the retina by reducing the directionality of the light.In other embodiments, the mirrored surface can be shaped to provide adifferent pattern of retinal illumination needed for a particular use.The mirrored surface 21 also prevents light from entering the centralaperture 12 of the lens cavity 15 and the viewing area of the viewinglens 7. In this sense, mirrored surface 21 serves a purpose similar tothe light baffle 6. Light from the LEDs 10, transmitted off of themirrored surface 21 and through light channel 4 to the retina 101,reflects back through the contact lens 3 and viewing lens 7 resulting inan image 100.

An embodiment of the present invention allows a practitioner controlover the illumination pattern by direct control of individual LEDs 10. Acontroller 17 is connected to each individual LED or a series of LEDs toallow a practitioner spatial, temporal, and intensity control over theLEDs 10. A practitioner can choose which LED lights are on and theirradiance. By illumination of only a few LEDs in the ring of LEDs, thisallows for selective sectoral illumination of the retina 101.Illumination can be focused on peripheral versus central retina,allowing a practitioner to focus on one area of the retina. Thismaintains an advantage over contemporary slit lamp illumination in thatlarger areas of the retina can be illuminated at one time that affordedby the slit beam. The image 100 also has significantly reducedreflections and enhanced image contrast compared to contemporarydesigns. This sectoral illumination capability is advantageous forreduction of the embodiment to practice. Patient tolerance toillumination varies significantly, and control of individual LEDbrightness allows an illumination pattern to be set that is bothcomfortable for the patient and allows evaluation and treatment ofspecific areas of the retina. This particular embodiment envisions useof a controller 17 with the LEDs 10 to allow for sectoral illumination.However, the particular embodiment used to control illumination levelsand allow sectoral illumination may comprise other methods, includingbut not limited to a diaphragm, LCD mask, or neutral density filter.There is no capability for this specific control of the illuminationpattern in contemporary designs, which limits their practical use insome patients.

In an embodiment, the controller 17 can be triggered by a camera flashto allow all of the LEDS 10 to turn on momentarily at high brightnessfor the purposes of retinal photography. In an embodiment, thecontroller 17 can be used to control the intensity of infrared LEDs toallow focusing of the image from the handheld lens and then controlinterspaced white LEDS, turning them on momentarily at high brightnessfor the purposes of retinal photography

FIGS. 8A-B illustrate a configuration of components in an assembled viewand exploded view, respectively, to implement the handheld lensembodiment, for example, but not limited thereto, as described in FIG.7. A LED mounting 32 surrounds the mirrored surface 21 and the LEDs 10are mounted on the interior surface of the LED mounting 32. The contactlens 3, LED housing 32, mirrored surface 21, and viewing lens 7 each fitwithin a LED housing 31 and casing 33. The configuration allows theobjective viewing lens 7 and casing 33 of the handheld lens to beseparated from the integrated illumination contained in LED housing 31.If a configuration for illumination is needed for a particularapplication of retinal imaging, one particular LED housing 31 providingone configuration of illumination can be replaced with another LEDhousing 31 providing another configuration of illumination. The LEDhousing 31 can also be changed depending on the size of the patient'seye, exemplified by use of the handheld lens on neonatal versus adultpatients. The interchangeability eliminates the need for separate lensesfor different patient populations.

FIG. 9 illustrates an embodiment providing for the use of xenon flashlighting 91 in place of LEDs 10. The xenon flash lighting 91 emits lightwhich is reflected off of the mirrored surface 21 and transmitted to thepatient's eye. Use of xenon flash lighting 91 provides for a higherintensity light than achieved by LED or fiber optic illumination andeliminates the need to fiber optically couple flash illumination to thehandheld lens. In an embodiment xenon flash lighting 91 would be usedfor retinal photography.

An embodiment of the present invention, illustrated in FIG. 10, providesfor a handheld lens 11 utilizing surface-mounted LEDs 41 on a curvedsurface 42 to illuminate a patient's retina 101. The surface-mountedLEDs 41 may be high-intensity white, infrared, or colored.Surface-mounted LEDs 41 may be positioned on curved surface 42 so as toprovide even illumination across the patient's retina. Light from thesurface-mounted LEDs 41 enters the light cavity 5 and is transmitted tothe patient's eye through the light channel 4 and contact lens 3. It isthrough the light channel 4 that light from the surface-mounted LEDs 41is transmitted to the retina 101. The light channel 4 may be a thinningof the contact lens 3, a portion of the contact lens 3 that differs inpower, a gap ground into or provided in the contact lens 3, a gap aroundor adjacent the contact lens 3, or a space behind or adjacent to thecontact lens 3. The light is multidirectional in nature due to the shapeof the curved surface 42. The curved surface 42 can be shaped to provideany pattern of illumination needed for a particular application of thehandheld lens. The curved surface 42 also serves to prevent the lightfrom entering the central aperture 12 of the lens cavity 15 and theviewing area of the viewing lens 7. Light from the surface-mounted LEDs41, transmitted through the light channel 4 to the retina 101, reflectsback through the contact lens 3 and viewing lens 7 resulting in theimage 100.

The embodiment of FIG. 10 provides a matrix of the surface-mounted LEDs41 to allow an exquisite degree of temporal and spatial control ofretinal illumination not available in contemporary designs. Thisembodiment may be may be advantageous in using the invention in somepatient populations depending on application or patient constraints. Inparticular, placement of the surface-mounted LEDs 41 directly on thecurved surface 42 allows for a smaller LED housing 31 than in otherembodiments, which may be needed for certain patient populations such asneonates, or for particular applications such a vitreoretinal surgery.

The surface-mounted LEDs 41 can be individually controlled as describedfor the embodiment of FIG. 8 to allow any pattern of central orperipheral retinal illumination to be provided for the particularapplication. An embodiment of the present invention allows apractitioner control over the illumination pattern by direct control ofindividual surface-mounted LEDs 41. A controller 17 is connected to eachindividual LED or a series of LEDs to allow a practitioner spatial,temporal, and intensity control over the surface-mounted LEDs 41. Apractitioner can choose which LED lights are on and their radiance. Byillumination of only a few LEDs in the ring of LEDs, this allows forselective sectoral illumination of the retina. Illumination can befocused on peripheral versus central retina, allowing a practitioner tofocus on one area of the retina 101. This maintains an advantage overcontemporary slit lamp illumination in that larger areas of the retinacan be illuminated at one time that afforded by the slit beam. The image100 also has significantly reduced reflections and enhanced imagecontrast compared to contemporary designs. This sectoral illuminationcapability is advantageous to practical use of the invention. Patienttolerance to illumination varies significantly, and control ofindividual LED brightness allows an illumination pattern to be set thatis both comfortable for the patient and allows evaluation and treatmentof specific areas of the retina. This particular embodiment envisionsuse of a controller 17 with surface-mounted LEDs 41 to allow forsectoral illumination. However, the particular embodiment used tocontrol illumination levels and allow sectoral illumination may compriseother methods, including but not limited to a diaphragm, LCD mask, orneutral density filter. There is no capability for this specific controlof the illumination pattern in contemporary designs, which limits theirpractical use in some patients.

In an embodiment, the controller 17 can be triggered by a camera flashto allow all the surface-mounted LEDs 41 to turn on momentarily at highbrightness for the purposes of retinal photography. In anotherparticular embodiment, the controller 17 can be used to control theintensity of infrared LEDs to allow focusing of the image from thehandheld lens and then control interspaced white LEDS, turning them onmomentarily at high brightness for the purposes of retinal photography.

FIGS. 11A-11B shows the outer casing of handheld lens 11 in an exemplaryembodiment of the present invention in side ways position and upwardposition, respectively. A battery compartment 110 is located on the sideof the handheld lens 11 to house batteries to power the illuminationsource, as well as to house the fiber optic cable 2 and light source 1,as required by some embodiments described above. The dimensions of thevarious embodiment of this invention may be less than, for example,approximately 20% of the size of commercial embodiments of contemporarydesigns. With a battery powering the self-contained illumination ofvarious embodiments, no external AC power source or external electricalor fiber optic cords are necessary to connect to the handheld lens. Thefocal point of the handheld lens remains at the standard distance toallow for ophthalmic slit lamp biomicroscopy by a trained practitionerwith this lens. While it may be advantageous to have the power sourceand/or light source provided integrally connected with the hand heldlens 11 or completely inside the hand held lens 11, it should beappreciated that it may be provided from an exterior source, or anycombination thereof.

While an intended use for this lens is directed towards clinical slitlamp biomicroscopy, the scope of its use and the claims with the currentinvention include additional applications. In one embodiment the lenswill be used for application of laser photocoagulation to the retina inpatients requiring this treatment such as diabetics and those withretinal defects. In an embodiment the laser aiming beam and laserapplication could be provided as conventionally occurs via the slit lampbiomicroscope. However, rather than using the slit illumination of theslit lamp to illuminate the retinal details, built in illumination inthe handheld contact lens would serve this function. This has thepotential to allow a 165 degree full illumination of the retina duringlaser application, which is not possible with contemporary designs. Italso allows for sectoral retinal illumination with significantly reducedimage aberrations than available with contemporary designs.

In an embodiment this lens may be adapted for use with existing retinalcameras or other image recording devices as desired or required. FIG.12A illustrates one such embodiment. The handheld lens 11, designed toprovide even illumination of a patient's retina 101 through providingannular illumination, is attached to a lens-to-camera interface 121. Thelens-to-camera interface 121 is also attached to an image recordingdevice 122. The lens-to-camera interface 121 comprises the optics andhousing needed to couple the image produced by the handheld lens to theimage recording device 122 to allow the handheld lens image to berecorded. Most conventional retinal cameras are capable of approximately60 degrees field of view of the retina, which encompasses only the mostcentral aspects of the retina. Widefield photography requires use of acontact lens, but is not possible with a standard retina camera due tothe design of the retina camera illumination. One particularimplementation of the embodiment illustrated in FIG. 12A is shown inFIG. 12B.

It should be appreciated that an aspect of the various embodiments ofthe invention provided throughout this disclosure may include images ordata obtained by handheld lens 11 that may be stored or communicatedwith the image recording device 122 as shown, or other devices notshown. For instance, images (or other data) may be communicated througha transmission module (not shown) to either a local and/or remotelocation(s). It should be appreciated that the local and/or remotelocation(s) may include, but are not limited thereto, a user, aprocessor, a display, a database, an archive, PDA, computer, lap top,network, or any combination thereof. This may enable specialists (orother practitioners or users) to complete diagnostics using the images(or other data) at local or remote locations and enable telemedicinepractices (e.g., internet practices, etc.) to be used. In usingtelemedicine practices (e.g., internet practices, etc.), the images orother data may be transmitted through the transmission module (hardwire,wireless, etc. as desired or required) to a remote location(s) wherethey are later reviewed by ophthalmologists or other trainedspecialists. If the image shows that the patient has a disease ordefect, the patient may then be referred to a specialist for moretesting and treatment. In this situation, images of the hand held lenssystem/device can be recorded at a primary care clinic without the needfor specialists at the primary care clinic to perform the diagnosis.Reviewing images by specialists at a remote location may allow for moreefficient processing and diagnostics of the recorded images or otherdata. This may allow a greater number of patients (or subjects) to bescreened for retinal diseases, etc. at a lower overall cost.

In an embodiment it is provided that xenon or LED illumination will beused built into the handheld lens 11. The retina camera can then beadapted to disable its illumination and rely on the self-containedhandheld lens illumination to enable widefield retinal photography.

FIG. 13A shows a view of a model eye using the embodiment of FIG. 10. Inthe image, only part of the retina 101 is illuminated. The controller 17is being used to selectively illuminate only this portion of the retina101.

FIG. 13B shows a view of a model eye using the embodiment of FIG. 10.Each of surface-mounted LEDs 41 is illuminated, illuminating thepatient's retina 101.

FIG. 13C shows an image taken by a contemporary retinal camera. Theimage is obscured by corneal haze. Comparing FIGS. 13B and 13C revealsthat the handheld lens of FIG. 10 is able to achieve a similar or higherquality image than contemporary retinal cameras.

In another embodiment this self-illuminated handheld lens 11 may be usedto adapt existing surgical vitreoretinal contact lenses used forvitreoretinal surgery. Handheld lens 11 will provide illumination of theretinal surface to enable better visualization during vitreoretinalsurgery. It would also potentially permit bimanual vitreoretinal surgeryas a separate handheld light fiber to illuminate the retina as used inconventional vitreoretinal surgery may no longer be necessary if thesurgical vitreoretinal contact lens provides sufficient illumination. Inone particular embodiment, individual control over the pattern ofretinal illumination would be provided using the controller 17 or othermethod, for example, as described for the embodiments of FIG. 7, FIG. 8,and FIG. 10.

Referring to FIG. 14, the objective lens 110 may preferably be a widefield aspherical lens and is located near a first end of the funduscamera 600. The objective lens 110 defines a symmetric viewing axis 111and a working plane 106 of the fundus camera 600. When a subject eye 101is aligned with the fundus camera 600 for fundus viewing, a subjectpupil 103 is about to position at the working plane 6 and the LEDillumination module 180 are projected into subject pupil 3 to illuminatethe subject retina 102 for alignment and for photographing. At a properalignment, the objective lens 110 produces a first retina image near itsback focal plane 105, and the first retina image is then re-imaged intothe digital camera 120. The illumination aperture 8 is located at theback focal plane 105 so as to define illumination area on the subjectretina 102. Also illustrated is subject crystalline lens 104.

At a proper alignment, objective lens 110 also forms an image of thesubject pupil 103 onto the plane of optical stop 114, which thus definesa small, virtual viewing window on the subject pupil 103 for the camera120 to look through into the retina 102.

In an embodiment, the wide field fundus camera 600 may require a staticfield of view of 120 degrees or wider on the subject retina 102. In anembodiment, the objective lens 110 has an optical power of about 120 Dand a diameter of about 18 mm. The objective lens 110 has thus a backfocal length of shorter than 8 mm and a small working distance ofapproximate 4 millimeters with respect to the subject cornea 107.

In an embodiment, a contact lens 112 is preferably positioned in frontof the aspherical objective lens 110 and in direct contact with thesubject cornea 107. The contact lens 112 may or may not have opticalpower. For example, in an embodiment, a contact lens 112 is incorporatedwith the aspherical objective lens 110 to produce a first retinal imageof the retina 102. In an embodiment, the contact lens may have adiameter of about 110 mm to fit for small eye ball 101 of the infants.

FIG. 15 shows schematically an embodiment of the front LED illuminationmodule 180 as shown in FIG. 14, and furthermore with an optional crosspolarization. The front LED illumination module 180 includes a pluralityof LEDs 181 a-181 n, a first polarizer 182, a light baffle 183, and asecond polarizer 184. The plurality of LEDs 181 a-181 n may be highbrightness, surface mounted, white LEDs. The LEDs are mounted in acircle around the symmetric viewing axis 111 of the objective lens 110.The first polarizer 182 is shaped and attached to cover the plurality ofLEDs 181 a-181 n, and the second polarizer positioned 184 is positionedin the viewing path of said digital camera 120. The light baffle 183 ismade of black to block direct view of the LEDs 181 a-181 n from thedigital camera 120. The light baffle 183 may be made of metal so that itcan also serve as a heat sink to the LEDs 181 a-181 n.

In an embodiment, the LEDs 181 a-181 n are positioned in a circle ofapproximate 7 mm in diameter. The light baffle 183 defines a viewingchannel of the objective lens 110 with an aperture of approximate 5.5mm.

FIG. 16 shows schematically a self-illuminated wide angle contact lens700 implemented having a front LED illumination module 180 with crosspolarization. The self-illuminated wide angle contact lens 700 consistsof primarily a contact lens 112, a front LED illumination module 180,and an objective lens 110. The front LED illumination module 180includes a plurality of LEDs 181 a-181 n, a first polarizer 182, a lightbaffle 183, and a second polarizer 184.

FIG. 17 shows a CAD drawing of self-illuminated wide angle contact lens800 implemented a front LED illumination module 180 with crosspolarization. The front LED illumination module 180 includes a pluralityof LEDs 181 a-181 n, a first polarizer 182, a light baffle 183, and asecond polarizer 184.

FIG. 18 shows a front view of FIG. 17 of a LED circular array 181 forfront LED illumination. In the embodiment, four LEDs form the pluralityof LEDs 181 a-81 n.

FIG. 19 shows a side view of FIG. 17 of a LED circular array 181 forfront LED illumination.

FIG. 20 shows a cross section drawing of a self-illuminated handheldlens 900 implemented having a front LED illumination module 180 withcross polarization. The self-illuminated handheld lens 900 consists ofprimarily a contact lens 112, a front LED illumination module 180, anobjective lens 110 and a lens housing 190.

FIG. 21 shows a side view of FIG. 20 of the self-illuminated handheldlens 900.

FIG. 22 shows a front view of FIG. 20 of the self-illuminated handheldlens 900.

In short, an aspect of the present invention provides a handheld funduslens with built in self-illumination to permit widefield viewing of theretina. Current handheld fundus lenses rely on external slit lampbiomicroscope illumination of the retina, which has the disadvantage ofsignificant image aberrations and reflections as well as a limited slitarea of retina that can be viewed at one time. The novel illuminationdesign of the various embodiment of the present invention overcomes allof these limitations to allow more detailed examination of the entireretinal surface in any pattern needed and permit safer surgicalprocedures to be performed on the retina.

Accordingly, the revolutionary medical device (and related method) ofthe various embodiments will allow retina specialists their first cleardetailed view of the retina during clinical exam at the slit lamp in 100years. Further, it has the potential to completely change the wayophthalmologists examine the retina, and to dramatically improve thestandard to which we are held on the detail of our clinical retina exam.It provides the potential to bring the same technological capabilitiesthat we currently have in retina photography to our day to day clinicalexamination of the eye. In some cases it may eliminate the need forseparate procedures to obtain retina photography as the photographicview at the ophthalmic slit lamp may be of sufficient. This device (andrelated method) can also potentially transform how both laser surgicalprocedures and vitreoretinal surgery is practiced. It will beimmediately clear exactly were the laser aiming beam is located on thesurface of the retina in a way which is not currently possible. Duringvitreoretinal surgery it may allow use of bimanual procedures, insteadof rendering one hand relegated to holding the illumination probe. Thisdevice will substantially improve patient care by increasing the qualityof the exam, allowing better diagnosis of retinal disease. It will alsorender laser and surgical procedures on the retina much safer byproviding a clear panoramic view of the retina. This is, simply put, oneof those few devices that has the possibility to transform how wepractice ophthalmology.

Commercial potential for this device (and related methods) is extremelyhigh. There is no competing technology currently in the marketplaceother than non-illuminated handheld fundus lenses with their associateddisadvantages. The commercial potential will be impacted by price pointover these existing lenses. It is therefore expected that ophthalmologyclinics in the United States and various countries around the world willpurchase these lenses if they are made available.

It should be appreciated that various sizes, dimensions, contours,rigidity, shapes, flexibility and materials of any of the embodimentsdiscussed throughout may be varied and utilized as desired or required.

It should be appreciated that as discussed herein, a subject may be ahuman or any animal. It should be appreciated that an animal may be avariety of any applicable type, including, but not limited thereto,mammal, veterinarian animal, livestock animal or pet type animal, etc.As an example, the animal may be a laboratory animal specificallyselected to have certain characteristics similar to human (e.g. rat,dog, pig, monkey), etc. It should be appreciated that the subject may beany applicable human patient, for example.

The devices, systems, compositions, computer program products, andmethods of various embodiments of the invention disclosed herein mayutilize aspects disclosed in the following references, applications,publications and patents and which are hereby incorporated by referenceherein in their entirety:

1. U.S. Pat. No. 3,944,341, Mar. 16, 1976, to Oleg Pomerantzeff,“Wide-Angle Ophthalmoscope and Fundus Camera.”

2. U.S. Pat. No. 5,822,036, Oct. 13, 1998, to Norbert Massie, “EyeImaging Unit Having a Circular Light Guide.”

3. U.S. Pat. No. 7,048,379, May 23, 2006, to Joseph Miller and JamesSchwiegerling, “Imaging Lens and Illumination System.”

4. International Patent Application Publication No. WO 2004/082465 A2,Miller, et al., “An Imaging Lens and Illumination System”, Sep. 30,2004.

In summary, while the present invention has been described with respectto specific embodiments, many modifications, variations, alterations,substitutions, and equivalents will be apparent to those skilled in theart. The present invention is not to be limited in scope by the specificembodiment described herein. Indeed, various modifications of thepresent invention, in addition to those described herein, will beapparent to those of skill in the art from the foregoing description andaccompanying drawings. Accordingly, the invention is to be considered aslimited only by the spirit and scope of the following claims, includingall modifications and equivalents.

Still other embodiments will become readily apparent to those skilled inthis art from reading the above-recited detailed description anddrawings of certain exemplary embodiments. It should be understood thatnumerous variations, modifications, and additional embodiments arepossible, and accordingly, all such variations, modifications, andembodiments are to be regarded as being within the spirit and scope ofthis application. For example, regardless of the content of any portion(e.g., title, field, background, summary, abstract, drawing figure,etc.) of this application, unless clearly specified to the contrary,there is no requirement for the inclusion in any claim herein or of anyapplication claiming priority hereto of any particular described orillustrated activity or element, any particular sequence of suchactivities, or any particular interrelationship of such elements.Moreover, any activity can be repeated, any activity can be performed bymultiple entities, and/or any element can be duplicated. Further, anyactivity or element can be excluded, the sequence of activities canvary, and/or the interrelationship of elements can vary. Unless clearlyspecified to the contrary, there is no requirement for any particulardescribed or illustrated activity or element, any particular sequence orsuch activities, any particular size, speed, material, dimension orfrequency, or any particularly interrelationship of such elements.Accordingly, the descriptions and drawings are to be regarded asillustrative in nature, and not as restrictive. Moreover, when anynumber or range is described herein, unless clearly stated otherwise,that number or range is approximate. When any range is described herein,unless clearly stated otherwise, that range includes all values thereinand all sub ranges therein. Any information in any material (e.g., aUnited States/foreign patent, United States/foreign patent application,book, article, etc.) that has been incorporated by reference herein, isonly incorporated by reference to the extent that no conflict existsbetween such information and the other statements and drawings set forthherein. In the event of such conflict, including a conflict that wouldrender invalid any claim herein or seeking priority hereto, then anysuch conflicting information in such incorporated by reference materialis specifically not incorporated by reference herein.

What is claimed is:
 1. A self-illuminated handheld lens for wide angleretinal viewing of a subject eye, comprising: an aspherical objectivelens having a symmetric viewing axis and defining a viewing channel;plurality of LEDs positioned around said viewing axis and configured toemit light to illuminate said subject eye; an electronic controllerpowering said plurality of LEDs and controlling each individual LED or aseries of LEDs independently; a light baffle configured to block straylight of said plurality of LEDs from getting into said viewing channel;and cross polarization means incorporated between said plurality of LEDsand said viewing channel of said aspherical objective lens, wherein saidcross polarization means comprises a first polarizer to polarize saidlight emitted from said plurality of LEDs and a second polarizerpositioned in said viewing channel of said aspherical objective lens. 2.The self-illuminated handheld lens of claim 1, further comprising: acontact lens positioned in front of said aspherical objective lens to beapplied to said subject eye.
 3. The self-illuminated handheld lens ofclaim 2, wherein said contact lens has a diameter approximate 10 mm. 4.The self-illuminated handheld lens of claim 1, wherein said asphericalobjective lens has a field of view of 120 degrees or wider on saidretina.
 5. The self-illuminated handheld lens of claim 1, wherein saidplurality of LEDs are each a high brightness, surface mounted, whitelight LED.
 6. The self-illuminated handheld lens of claim 1, whereinsaid light baffle is made of black outside said viewing channel.